System for the integrated and automated analysis of DNA or protein and method for operating said type of system

ABSTRACT

An embodiment of the present invention relates to a system for the integrated and automated analysis of DNA or protein, including a single-use cartridge, an analysis device comprising a control device, and devices for capturing and processing signals. An embodiment of the present invention relates, in particular, to the control device for carrying out a completely automatic process and evaluation of molecular diagnostic analysis via single-use cartridges (Lab-on-a-Chip). The first devices are provided for controlling an analysis process which occurs in the cartridge, subsequently the displacement and the thermostatisation of liquids, and the second devices are provided for processing the signals which are obtained during the analysis. The first and the second devices are synchronized in such a manner that the analysis process of the sample can be carried out in a totally integrated manner thus producing an immediate result.

PRIORITY STATEMENT

This application is the national phase under 35 U.S.C. §371 of PCTInternational Application No. PCT/EP2006/062499 which has anInternational filing date of Mar. 22, 2006, which designated the UnitedStates of America and which claims priority on German Patent application10 2005 024 610.9 filed May 25, 2005, the entire contents of which arehereby incorporated herein by reference.

FIELD

At least one embodiment generally relates to a system for the integratedand automated analysis of DNA or protein, for example one comprising asingle-use cartridge (card), an evaluation device and a device forsignal recording and processing. In particular, at least one embodimentof the invention generally relates to a control device as part of theevaluation device for the fully automatic processing and evaluation ofmolecular diagnostic analyses with disposable cartridges(“lab-on-a-chip” and also known as a biochip; see, commonly owned U.S.Patent Application Publication 2007/01411553). In addition, at least oneembodiment of the invention also generally relates to a method foroperating the type of system.

BACKGROUND

The significance of decentralized analysis devices (“point of care”,“near patient testing”) in molecular diagnostics or general medicaltechnology is increasing. In addition, fast tests are becoming more andmore important in the areas of foodstuff monitoring and environmentalprotection.

The general literature, but also especially the patent literatureincludes a large number of publications on the aforementioned topic: WO02/072 262 A1 and WO 02/073 153 A1 disclose systems for application inbiomedical technology in which samples taken in a decentralized mannerare evaluated in a decentralized manner by means of an optionally mobileread-out device. The samples, in particular, are in this case collectedin a single-use cartridge formed like a check card (“card”).

Such a cartridge for application in the DNA analysis of whole bloodsamples is disclosed in detail in WO 2006/042 838 A1, not previouslypublished. In this case, the following features of the cartridge areregarded as essential for automatically carrying out all the measuresrequired for process analysis from individual partial processes in thecartridge:

-   -   the cartridge contains a system of microchannels and/or        microcavities for a microfluidic process technology,    -   the microchannels or the microcavities have predetermined        geometrical structures for receiving reagents, wherein    -   the reagents are stored in a storage-stable form at specific        locations in the microchannels or the microcavities of the        cartridge,    -   means are present for providing the dry-stored reagents for the        respective partial process in a suitable form, in particular as        a liquid reagent.        Reference is expressly made to the disclosure of these features        in the above earlier application.

Furthermore, US 2002/0 179 444 A1 and US 2003/0 148 530 A1 discloseindividual solutions for a blood diagnosis method and the associatedsignal processing. Specific problem solutions for the realization of thesystem of the type mentioned in the introduction comprising thepreviously described card and associated suitable means for evaluationare described in earlier applications in the name of the applicant thathave not yet been published.

SUMMARY

At least one embodiment of the invention is directed to a system whichmeets practical requirements in particular with regard to the evaluationdevice. At least one embodiment is directed to an associated controlmethod for evaluation in the case of a system comprising cartridge andevaluation device. In the case of at least one embodiment, the followingrequirements are made of the evaluation device:

-   -   low price    -   small structural design    -   simple operating control (“one button” operation)    -   rapid performance of the analysis    -   integrated microfluidics    -   safety against contamination, i.e. avoidance of instances of        soiling and infections-high operational reliability    -   capability of communication with data processing systems.

No practically suitable solution has been disclosed hitherto for thefully automatic nucleic acid analysis from taking the sample (e.g.blood) to displaying the result, in particular including celldisruption, PCR and detection. Since the equipment currently proposedfor biochemical analysis does not yet meet all the practicalrequirements, at least one embodiment of the invention improves thesystem so as to allow a maximally automated and reproducible evaluation.In particular, the intention here is to ensure that the result isdisplayed directly on a display or the data are forwarded into acomputer system. The intention is to specify, in at least oneembodiment, a suitable operating method for this purpose.

The operating method of at least one embodiment for carrying out anevaluation of a sample in a single-use cartridge with the aid of thecontrol device in a system. Especially the realizations for carrying outa DNA analysis, and also in particular an SNP analysis, or alternativelya protein analysis, are contained in further embodiments of the method.

The basis of at least one embodiment of the invention, therefore, is animproved concept by comparison with the prior art: a device constructionrealized in accordance with this concept is designed according to atleast one embodiment of the invention for the fully automatic processingand evaluation of molecular diagnostic analyses with disposablecartridges (lab-on-a-chip), in particular for the control and read-outof analysis processes within cartridges in the form of modified checkcards.

In the case of at least one embodiment of the invention, the controldevice has the following features, in particular:

-   -   a cartridge receptacle for receiving, locking, unlocking and        releasing the cartridge,    -   a device for correctly positioning the cartridge in the reader,    -   sensors for identifying the cartridge, in particular a correct        cartridge, e.g. limit switches, barcode,    -   a water reservoir for diluting the sample, dissolving dry        reagents of the cartridge, carrying out flushing operations,        wherein fluidic contact can be made with the water reservoir by        way of a septum being pierced by a pointed hollow needle,    -   a sterile filter ventilation valve for ventilating the water        reservoir when water is drawn,    -   a power supply unit,    -   a pump for conveying extremely small quantities of liquid, for        example in the microliters range,    -   means for distributing water via valves, e.g. water-carrying        solenoid valves,    -   a pressure sensor in the water feed for monitoring fluidic        operations,    -   at least one interface for feeding water into the cartridge,    -   sensors for identifying the filling of throughflow channels on        the cartridge, e.g. capacitive sensors with electrodes above and        below the cartridge,    -   a device for closing off and opening venting openings of the        cartridge, e.g. air-carrying solenoid valves,    -   a device for closing off and opening chambers, in particular the        PCR chamber, on the cartridge, e.g. plungers pressing onto a        film,    -   a combination comprising a magnetic bead collector and a        thermostatic regulation device for capturing magnetic beads and        for carrying out thermocycling processes for the PCR,    -   a sandwich arrangement of two abovementioned devices for rapid        thermocycling,    -   a device for ensuring optimum heat transfer between the        thermostatic regulation device and cartridge, e.g. by way of a        contact pressure defined by way of springs,    -   a device for making electrical contact with an electrical        detection module, e.g. contact pins,    -   an integrated thermostatic regulation for the detection module,    -   control, measuring and regulating electronics for all the        functions,    -   a microcontroller for control and data acquisition, and    -   a display for representing the analysis results.

In the associated method for operating the control and read-out devicefor the evaluation of a cartridge filled with a sample, the followingmethod steps are carried out specifically for a DNA analysis:

-   -   the cartridge receptacle is opened and the pump draws water from        the reservoir given a suitable valve position,    -   the control device indicates readiness for operation,    -   a user inserts the cartridge with a sample, e.g. blood,    -   the analysis is started by a “one button” action or        automatically, e.g. by way of a cartridge limit switch,    -   given a suitable valve position, water is pumped into the        cartridge via a water port in order to wash out excess sample        material,    -   the venting valves are actuated in a suitable manner in order to        allow or prevent the filling of cartridge channels by way of        permitting or avoiding venting,    -   as a result of the inflow of water, the sample is diluted and        pumped into the cell disruption channel, wherein dry reagents        are dissolved,    -   a residence time ensues for cell disruption, wherein liberated        DNA binds to magnetic beads,    -   nearly at the same time two ELISA reagent channels are filled,        wherein dry ELISA reagents (enzyme label and substrate) are        dissolved,    -   the content of the cell disruption channel is flushed by further        pumping of water through the PCR chamber, wherein the magnetic        beads with DNA are held back by a magnetic field, the remainder        is flushed into a waste channel,    -   the valves of the PCR chamber are closed off,    -   the thermocycling is started, wherein dry PCR reagents are        dissolved,    -   a predetermined number of thermocycles are carried out at        defined temperatures (PCR),    -   the valves of the PCR chamber are opened after conclusion of the        PCR,    -   given a suitable valve position, water is pumped into the        cartridge via a further water port and the PCR product is        flushed from the PCR chamber into a detection chamber,    -   the detection chamber is thermostatically regulated, wherein        hybridization of the DNA with catcher molecules takes place,    -   air possibly present between the PCR product and the dissolved        ELISA reagents is pumped into a waste channel by suitable        setting of water port and venting valves,    -   the dissolved enzyme label is pumped via the detection chamber        into a further waste channel by suitable setting of water port        and venting valves,    -   the dissolved substrate is pumped via the detection chamber into        a further waste channel by suitable setting of water port and        venting valves,    -   the electrical detection is started,    -   e.g. an SNP analysis is carried out by recording melting curves.

As an alternative to the above method sequence, a protein analysis isalso possible, wherein no cell disruption and no PCR are necessary. Inthis case, the proteins sought are isolated from the sample by way ofmagnetic beads and detected in the detection chamber. Haptens can bedetected analogously.

An analysis process integrated throughout is carried out, then, by themethod according to an embodiment of the invention. This is understoodto be a fully automated method sequence without manual intervention.After the introduction of the cartridge with the sample into the controldevice, the sample treatment and analysis process proceeds automaticallyuntil the actual detection of the substances sought. This has theadvantage, in particular, of high reproducibility and a low error rate.

What is particularly advantageous in the system according to at leastone embodiment of the invention is that the control device can beembodied in compact fashion and has both internal fluidic interfaces andelectrical interfaces. Interfaces for linking to external computersystems are additionally present. These may be serial and/or wirelessinterfaces, for example. In an example embodiment, the control devicecomprises a connection possibility for a commercially available PDA.This enables a display to be integrated into the control device in asimple manner. In a particularly preferred example embodiment, a displayand operating unit is fixedly integrated into the control device.

With the system according to at least one embodiment of the invention, aconsiderable advance is achieved compared with the previously proposeddevices. It is now possible, for example, for the measured data to bedirectly displayed or forwarded for evaluation.

BRIEF DESCRIPTION OF THE DRAWINGS

Further details and advantages of the application are explained on thebasis of the example embodiment described below in association with theaccompanying drawings, in which:

FIG. 1 shows a schematic overview diagram of an analysis device,

FIG. 2 shows a schematic overview diagram of a cartridge,

FIG. 3 shows a schematic flowchart of an analysis method,

FIG. 4 shows a schematic overview diagram of the functional units of thecontrol device,

FIG. 5 shows a schematic overview diagram of the fluidic components ofthe control device,

FIG. 6 and FIG. 7 show schematic illustrations of a measuring device fora filling level,

FIG. 8 shows a schematic illustration of a fluidic interface between thecartridge and the control device,

FIG. 9 shows a schematic illustration of a venting interface between thecartridge and the control device,

FIG. 10 shows a schematic illustration of a PCR chamber of thecartridge, and

FIG. 11 shows a schematic illustration of a detection chamber of thecartridge.

DETAILED DESCRIPTION OF THE EXAMPLE EMBODIMENTS

An analysis device is described below as one example embodiment of theinvention. The analysis device is divided into a control device and acartridge. Whereas the cartridge is, for example, present as adisposable article on which the actual analysis process proceeds, thecontrol device is reusable and serves for controlling the analysisprocess. The cartridge contains only passive components; the entirecontrol proceeds from the control device.

FIG. 1 shows the construction of the analysis device. It includes acartridge 101, which can be inserted into a cartridge receptacle 103 ofa control device 105. The cartridge receptacle 103 is connected to apower supply unit 107, which supplies the receptacle with power. For thetransmission of data of the analysis process, the cartridge receptacle103 is additionally connected to an electronic unit 109. The data can beoutput from the electronic unit 109 via an interface 111.

The interface 111 is formed as an RS232 interface, for example. Theelectronic unit 109 is connected to the power supply unit 107 for itspower supply.

In order to carry out the analysis process, water is required in thecartridge. This water is stored in a supply container 113. The supplycontainer 113 is a commercially available bottle containing sterile,distilled water, for example, which is closed off by a septum. Acorresponding receptacle for the bottle in the control device isprovided with a cannula which pierces the septum when the bottle isinserted. As a result, the water becomes accessible and it can be drawnfrom the bottle via a connected pump 115. The pump 115 can take up adefined quantity of water and pump it into the cartridge receptacle 103via a connection. The water passes into the cartridge 101 via thecartridge receptacle 103 and is available in the analysis process. Thepump 115 is connected to the power supply unit 107 for its power supply.

FIG. 2 schematically illustrates the cartridge 101, which has alreadybeen disclosed in detail in WO 2006/042 838 A1 and corresponding U.S.Pat. No. 7,851,227, not previously published, which disclosure is alsothe subject matter of the present patent application, wherein the entirecontents thereof is hereby incorporated herein by reference.

The cartridge 101 is present in the form of a plastic card 201 of thesize of a check card and comprises a number of channels. Via a sampleport 203, a sample can be pipetted into the cartridge 101. Water can beintroduced into the cartridge 101 via four water ports 205, 205′, 205″and 205′″. The cartridge 101 is additionally provided with four ventingports 207, 207′, 207″ and 207′″, through which air can escape when thechannels are filled. A metering section 209 comprises a volume of 1 land services for tapping of this quantity from the sample that has beenpipetted in. A sample waste channel 211 serves for receiving the rest ofthe sample. The venting port 207′″ lies at the end of the sample wastechannel 211. The metering section 209 is adjoined by a cell disruptionchannel 213, in which reagents for the cell disruption are stored in dryform. It is only as a result of the introduction of the sample indiluted form that the reagents are dissolved and cell disruption takesplace. As a result of the cell disruption, DNA contained in the cells isliberated, said DNA binding to magnetic beads likewise present in thecell disruption channel 213.

The cell disruption channel 213 is connected to a PCR chamber 215, inwhich a PCR can be carried out. The PCR chamber 215 can be closed off byway of two valves 217. The required reagents are situated in the PCRchamber 215 likewise in dry form. Arranged downstream of the PCR chamber215 is a PCR waste channel 219 connected to the venting port 207″. Awater channel 221 connected to the water port 205″ leads in at one endof the cell disruption channel 213. The PCR chamber 215 is connected toa detection chamber 223, in which the DNA can be detected by means of asensor array. The detection chamber 223 is connected to two wastechannels 225 and 227 ending in the ventilation ports 207′ and 207,respectively. In addition, the detection chamber 223 is connected to twoELISA reagent channels 229 and 231 (ELISA: enzyme linked immuno sorbentassay), which, for their part, are connected to the water ports 205′ and205, respectively. ELISA reagents 232 are stored in dry form in theELISA reagent channels 229 and 231, and after being dissolved in watercan be flushed into the detection chamber 223.

FIG. 3 shows a schematic flowchart of an analysis process. In a firstmethod step Si, the cartridge is prepared. This involves pipetting thesample into the cartridge and possibly providing water in the controldevice. As it is pipetted in, the sample accumulates in the sample wastechannel 211 of the cartridge (referring to FIG. 2), the metering section209 likewise filling up in the process. In a second method step S3, thecartridge is introduced into the control device. As a result of theintroduction of the cartridge, valves situated in the read-out deviceare connected to the water ports 205 to 205′″, and the venting ports 207to 207′″, such that water can be introduced into the cartridge and aircan escape. Moreover, a switch in the read-out device is actuated,whereupon the analysis process starts automatically.

In this case it is ensured by way of functional elements known per sethat the cartridge is in the correct position and has the correctorientation. Moreover, the fact of whether the cartridge is one which issuitable for the control device is identified. At the beginning of theanalysis process within the cartridge 101, the water channel 221 isfilled with water, the water channel 221 likewise being vented via thePCR waste channel 219. This simplifies the method sequence since the airpresent in the water channel 221 could not escape in the furthersequence.

In a third method step S5, water is pumped into the water port 205′″,such that that portion of the sample which is situated in the meteringsection 209 is isolated. The venting port 207′″, which is otherwiseclosed off by the valve, is opened for this purpose. As soon as thesample waste channel 211 has been filled, the venting port 207′″ isclosed off again in a fourth method step S7. The filling level of thesample waste channel 211 is measured by way of filling level sensorsarranged in the control device. The functioning is explained withreference to FIGS. 6 and 7.

As a result of the venting port 207′″ being closed off, pressure startsto build up as water continues to be pumped in, such that that portionof the sample which is situated in the metering section 209 is flushedinto the cell disruption channel 213. The valve assigned to the ventingport 207″ in the control device is opened for this purpose. The sampleis diluted with water. As a result of the introduction of the dilutedsample, the dry reagents in the cell disruption channel 213 aredissolved whereupon cell disruption takes place in a fifth method stepS9. DNA situated in the cells of the sample is liberated in this case.The liberated DNA binds to magnetic beads stored in the cell disruptionchannel 213.

At the same time as the cell disruption, in a sixth method step S11, theELISA reagent channels 229 and 231 are filled with water. The valvesassigned to the venting ports 207′ and 207 in the control device areopened for this purpose. The filling level of the ELISA reagent channels229 and 231 is measured by filling level sensors arranged in the controldevice.

After the cell disruption has been concluded, in a seventh method stepS13, the diluted sample with the magnetic bead-DNA complexes is flushedthrough the PCR chamber 215. For this purpose, as already previously,water is pumped through the water port 205′″ and the venting port 207″is opened. In the control device, there is a magnet arranged above thePCR chamber 215, the magnetic bead-DNA complexes being held back in thePCR chamber 215 by said magnet. The remainder of the diluted sample isflushed into the PCR waste channel 219. In an eighth method step S15,water is again pumped through the PCR chamber 215, thereby cleaning themagnetic bead-DNA complexes.

In a ninth method step S17, the valves 217 of the PCR chamber 215 areclosed. In a tenth method step S19, the DNA of the magnetic bead-DNAcomplexes is replicated by a PCR. For this purpose, correspondingreagents are situated in the PCR chamber 215 in dry form, said reagentsbeing dissolved by the addition of water. In order to manipulate thetemperature in the PCR chamber 215, two Peltier units are situated inthe control device. After the conclusion of the PCR, in an eleventhmethod step S21, the valves 217 of the PCR chamber 215 are opened. In atwelfth method step S23, water is pumped into the channel 221 via thewater port 205″, such that the water previously situated in the channel221 is flushed into the PCR chamber 215. The channel 221 contains drystored salts which are thus added to the PCR product, that is to say thereplicated DNA. At the same time, the replicated DNA is flushed from thePCR chamber 215 into the detection chamber 223. In this case, theventing ports 207″ and 207′ are closed, and the venting port 207 isopen.

In a thirteenth method step S25, a hybridization between the PCR productand capture molecules arranged in the detection chamber 223 takes placein the detection chamber 223. In order to support the hybridization, thetemperature in the detection chamber 215 is set in a defined manner byway of a Peltier element arranged in the control device. In a fourteenthmethod step S27, a label enzyme (e.g. streptavidin alkaline phosphatase,streptavidin esterase or oligonucleotide-coupled esterase) linked to acoupling molecule is pumped from the ELISA reagent channel 231 throughthe detection chamber. For this purpose, water is pumped through thewater port 205 and the venting port 207′ is opened. The DNA linked tothe catcher molecules is marked by the label enzyme. In a fifteenthmethod step S29, a dissolved enzyme substrate is pumped from the ELISAreagent channel 229 through the detection chamber 215. Both enzyme labeland enzyme substrate channel are vented before the flooding of thedetection chamber 231 via the channel 227 in order to prevent air frombeing entrained into the detection chamber 223. By virtue of thesubstrate, a so-called redox cycling process occurs in the detectionchamber, and the bound DNA can be detected by said process. Evaluationof the measurement data correspondingly takes place in a sixteenthmethod step S31.

FIG. 4 illustrates the central components of the control device 105 in ablock diagram. A microcontroller 401 serves as central controller of theentire analysis process, the microcontroller being connected to acomputing unit 403 via a serial RS232 interface 402. The computing unit403 is a commercially available PDA, for example, and serves forrecording measurement data from the analysis process. The computing unit403 is equipped with a radio module 404, via which the measurement datacan be transmitted to an evaluation unit 405. The radio module 404communicates with the evaluation server 405 for example by infrared,BLUETOOTH® or WLAN.

The microcontroller 401 controls all the components of the controldevice 105 which are involved in the analysis process. The cartridgereceptacle 103 comprises a stepper motor 407, which moves a part of thecartridge receptacle 103 upon insertion of the cartridge, such that thecartridge is correctly received. The Peltier elements are brought intoposition in this case. A limit switch 409 interrupts the process whenthe cartridge has been completely introduced. As a result of theintroduction process, the water ports and the venting ports areconnected to corresponding channels in the control device. Valves 413controlled by the microcontroller 401 are arranged in the channels. Asignal processing unit 415 serves for communicating the control signals.The arrangement and functioning of the channels and valves are explainedwith reference to FIG. 5.

For the movement of the water in the channels, the pump 115 iscontrolled by the microcontroller 401. Its piston is moved by a steppermotor 417, which is in turn controlled by means of an output stage 419and a limit switch 421. The pressure in the pump 115 is measured bymeans of a pressure sensor 423 and read out by the microcontroller 401via a signal processing unit 425.

The movement of the water in the cartridge is monitored by means offilling level sensors 427, which are read by the microcontroller 401 viaa signal processing unit 429.

The valves of the PCR chamber are controlled via a servomotor 431 and asignal processing unit 433. Three Peltier elements 435 and temperaturesensors 437, which are controlled and read via a PID controller 439 andan output stage 441, serve for the thermostatic regulation of the PCRchamber and the detection chamber. The PID controller 439 is controlledby the microcontroller 401 via a signal processing unit 443.

The signals generated by the redox cycling on the sensor array aremeasured via a contact-making module 445 and forwarded to a signalprocessing unit 451 via read-out circuits 447 and a multiplexer 449. Thesignal processing unit 451 is connected to the microcontroller. Thenecessary control voltages, such as e.g. a reference voltage and acounter-voltage of a potentiostat, are fed to the sensor array via thecontact-making module 445. The sensor array is embodied as a CMOS sensorchip, for example. In this case, the contact-making module 445advantageously has the arrangement as in a commercially available smartcard reader.

FIG. 5 illustrates a schematic overview diagram of the fluidiccomponents of the control device. The cartridge receptacle 103 includesfour water ports 503, 503′, 503″ and 503′″, which are connected to thewater ports of the cartridge when the latter has been inserted. Fourventing ports 505, 505′, 505″ and 505′″ are likewise provided, which areconnected to the corresponding venting ports of the cartridge. Thecartridge receptacle 103 furthermore includes three filling levelsensors 507, 507′ and 507″, the functioning of which is explained withreference to FIGS. 6 and 7. They operate capacitively and comprise twocapacitor plates. In order to ensure a simple construction of thecartridge receptacle 103, one capacitor plate 509 is formed inlarge-area fashion and is used jointly for all the filling level sensors507, 507′ and 507″. The other capacitor plates 511, 511′ and 511″ arecorrespondingly embodied separately.

The filling level sensors 507 and 507′ are designed in each case formonitoring two channels of the cartridge and are arranged atcorresponding locations of the cartridge receptacle 103. The fillinglevel sensor 507 serves for monitoring the two ELISA reagent channels229 and 231, while the filling level sensor 507′ monitors the samplewaste channel 211 and the PCR waste channel 219. The filling levelsensor 507″ serves for monitoring the waste channel 227.

Two motors 503 for controlling two actuators 515 are additionallyarranged in the cartridge receptacle 103. The actuators 515 serve foropening and closing the valves of the PCR chamber on the cartridge.

The water required for the analysis process comes from a commerciallyavailable bottle 517, which is closed off by a septum 519. The bottle517 is held by a receptacle 521 of the control device, two cannulas 523and 525 being arranged in said receptacle. When the bottle 517 isintroduced into the receptacle 521, the septum 519 is pierced by the twocannulas 523 and 525 and the water in the bottle 517 is made accessible.The cannula 523 is connected to a pump 115 via a line 527 and athree-way valve 529. By means of the pump 115, a volume of water thatcan be set in a defined manner can be drawn from the bottle 517. Thepump 115 comprises a hollow cylinder 533 with a movable piston 535. Thepiston 535 can be moved in a defined manner by means of a stepper motor537. A pressure sensor 539 is arranged in the line 527, and the pressurein the line 527 can be determined by way of the pressure sensor.

The cannula 525 serves for ventilating the bottle, since a negativepressure would otherwise arise when water is drawn. The cannula isconnected to a sterile filter 541, via which air can pass into thebottle.

The three-way valve 529 can be connected to the four water ports 503,503′, 503″ and 503′″ via a line system 543. A plurality of lines 527′and three further three-way valves 5291, by which the three-way valve529 can be selectively connected to each of the water ports 503, 503′,503″ and 503′″, are provided for this purpose. Through suitableswitching of the three-way valves 529′, the water can thus be pumpedfrom the hollow cylinder 533 into one of the water ports 503, 503′, 503″or 503′″. The pressure occurring in the line system 543 and the line 527is detected by the pressure sensor 539 in this case.

The air present in the channels of the cartridge before the start of theanalysis process must be able to pass out of the cartridge as the latteris filled with water. The four ventilating ports 505, 505′, 505″ and505′″ are provided for this purpose in the cartridge receptacle. Theyare connected via lines 545 to two-way valves 547, which can beoptionally closed or open. When water is introduced into one of thechannels, the corresponding one of the valves 547 is opened, such thatair can escape from the cartridge.

FIGS. 6 and 7 show the functioning of the filling level sensors. FIG. 6illustrates the control device 105 in a sectional view. A cartridge 101has been introduced into the cartridge receptacle 103. In the cartridgereceptacle 103, two capacitor plates 607 and 609 are arranged above andbelow the cartridge 101. The capacitor plates 607 and 609 are connectedto a measuring unit 611, by which the capacitance of the capacitorformed by the capacitor plates 607 and 609 can be determined.

In FIG. 6, a channel 613 shaped within the cartridge 101 is partlyfilled with water 615. In the illustration in FIG. 7, the channel 613 isfilled to an extent such that there is water 615′ between the capacitorplates 607 and 609. As a result, the capacitance of the capacitor isaltered in comparison with the state illustrated in FIG. 6. The changeis determined by means of the measuring unit 611 and the liquid level inthe channel is determined in this way.

FIG. 8 shows a section through a part of the cartridge receptacle 103with cartridge 101 inserted. The contact-making between the water portsof the control device 103 and the cartridge 101 is shown. A channel 707is milled in a plastic body 705 of the cartridge 101. The channel 707 iscovered by way of an adhesive film 709, the adhesive film 709 beingadhesively bonded onto the plastic body 705. The adhesive film 709 iscommercially available and compatible with all the processes thatproceed in the cartridge 101. A further adhesive film 711 is fixed tothe water port of the cartridge 101. The further adhesive film can bepierced by a hollow needle 713 arranged in the cartridge receptacle 103and the fluidic contact between the cartridge receptacle 103 and thecartridge 101 can thus be established. A seal 715 that prevents liquidsfrom escaping is arranged in the cartridge receptacle 103. the seal 715is preferably composed of a biochemically compatible silicone materialin order to avoid contamination of the water ports.

Before the cartridge 101 is introduced into the cartridge receptacle103, an upper part 717 and a lower part 719 of the cartridge receptacle103 are further away from one another than illustrated in FIG. 8. Thisenables the cartridge 101 to be introduced in a convenient manner. Assoon as the cartridge 101 has been completely introduced, the two parts717 and 719 are brought together and the cartridge 101 is locked in thecartridge receptacle 103. At the same time, the adhesive film 711 ispierced by the hollow needle 713.

FIG. 9 shows a section through a part of the cartridge receptacle 103with inserted cartridge 101 at one of the venting ports. In thecartridge 101, analogously to the illustration in FIG. 8, a channel 707′is milled into the plastic body 705, said channel being covered by theadhesive film 709. Around the venting port 721 of the cartridge 101, adepression is milled into the plastic body 705, an adhesive layer 723being arranged in said depression. A Teflon membrane 725 is fixed on theadhesive layer 723. A seal 715 is arranged in the lower part 719 of thecartridge receptacle 103. A channel 727 is additionally provided, whichruns through the seal 715 and is therefore in contact with the Teflonmembrane 725. A hose 729 connected to the venting valves of the controldevice is arranged in the channel 727.

The Teflon membrane 725 ensures that no liquid can escape from thecartridge. This serves to avoid contamination of the control device,which is intended to be able to be used for a multiplicity of analysisprocesses. The sample introduced into the cartridge 101 generallycontains infectious biomaterial which would contaminate the controldevice upon contact, and the control device would therefore have to becleaned or replaced for carrying out further analysis processes. TheTeflon membrane 725 is permeable to vapor and gas, but impermeable toliquids. By way of the pressure sensor 533 of the control device it isensured that the pressure in the cartridge 101 does not becomeexcessively high and the Teflon membrane 725 or the adhesive film 709 isnot damaged or torn.

FIG. 10 illustrates a section through a part of the cartridge receptacle103 with inserted cartridge 101. Analogously to FIGS. 8 and 9, a channel707″ is milled into the plastic body 705. The channel 707″ has awidening serving as a PCR chamber 731. The channel 707″ and the PCRchamber 731 are covered by the adhesive film 709.

In order to ensure rapid heat transfer for the thermocycling during thePCR, the PCR chamber 731 is kept as small as possible in a geometricaldimension (approximately 1 mm or volume<20 μl) and the heat transfersare realized in a “sandwich” thermostatically regulating arrangementsuch that only small liquid layers (a few 100 μm) have to be brought tothermal equilibrium. The PCR chamber 731 is preferably situated in ahousing with plane-parallel outer surfaces (plastic body 705 with cutoutand adhesive film 709).

In the cartridge receptacle 103, two thermal coupling plates 733 and733′, for example composed of aluminum, are arranged above and below thePCR chamber 731 of the cartridge 101. The two thermal coupling plates733 and 733′ are pressed against the adhesive film 709 and against theplastic body 705, respectively, and serve for transmitting thermalenergy of two Peltier units 735 and 735′ into the PCR chamber 731 when aPCR is carried out. The Peltier units 735 and 735′ are in thermalcontact with two heat sinks 737 and 737′ which serve for dissipatingheat during the cooling operations of the PCR cycles. They have alargest possible surface area in order to enable an efficient heattransfer to the ambient air, if appropriate with the aid of fans.

A cutout 739 is shaped in the thermal coupling plate 733. By virtue ofthe cutout 739, the adhesive film 709 can bulge out in the event ofpossible excess pressure, for example during a temperature increase in aPCR cycle.

Two permanent magnets 741 and 741′ are arranged centrally above andrespectively below the heat sinks 737 and 737′. The magnetic fieldgenerated by the permanent magnets 737 and 737′ serves for holding backmagnetic beads when the latter are flushed through the channel 707″ intothe PCR chamber 731. The DNA bound to the magnetic beads is thus heldback for later replication by the PCR in the PCR chamber 731.

The field gradient generated by the two permanent magnets 741 and 741′is too small, however, to efficiently hold back the magnetic beads. Inorder nevertheless to obtain a high field gradient in the PCR chamber731 along the throughflow direction of the liquid containing themagnetic beads, the thermally conductive but magnetically neutralthermal coupling plates 733 and 733′ are equipped with small-volumebodies 743 and 743′ (approximately 5 mm³) composed of a material havinga high relative permeability μ(r), in conjunction with still goodthermal conductivity, preferably permalloy (Ni—Fe) or Mumetal(Ni/Fe/Cu/Mo).

The small-volume bodies 743 and 743′ respectively form a magnetic coredirectly at the surfaces of the PCR chamber 731. The PCR chamber 731 isthen situated directly between the magnetic cores. The magnetic coresare magnetized by the magnetic field of the permanent magnets 741 and741′. The magnetic field lines are concentrated by way of the magneticcores, whereby a high field gradient is generated.

In the field gradient arranged parallel to the outer walls of the PCRchamber 731 and flow direction of the solution containing magneticbeads, the magnetic beads are drawn in, detained and thereforeconcentrated.

The PCR chamber 731 can be closed up by way of two plungers 745 and745′. The plungers 745 and 745′ can be pressed against the adhesive film709 by way of springs and cams that are not illustrated here, such thatthe PCR chamber 731 is closed off.

The heat sinks 737 and 737′ are connected to screws 761 via springs 759.The screws 761 are screwed into the cartridge receptacle 103. Thethermal coupling plates 733 and 733′ connected to the heat sinks 737 and737′, respectively, are pressed against the adhesive film 709 and theplastic body 705, respectively, by the springs 759, such that goodthermal contact arises. At the same time, thermal contact between thethermal coupling plates 733 and 733′ and the cartridge receptacle 103 isavoided to the greatest possible extent.

FIG. 11 illustrates a section through a part of the cartridge receptacle103 with inserted cartridge 101. A further channel 707′″ is milled intothe plastic body 705, said further channel being covered with theadhesive film 709. A chip module 747, by means of which the DNAcontained in the sample can be detected, is arranged in the plastic body705. By way of example, a redox cycling process for detecting the DNAcan take place on the chip module 747.

In order to support the hybridization between the DNA and correspondingcapture molecules that takes place at the surface of the chip module747, the chip module 747 is thermally coupled to a Peltier element 753via a thermal coupling plate 751. The Peltier element 753 is thermallycoupled to a cooling unit 755. The temperature in the vicinity of thechip module 747 can be monitored by way of a temperature sensor 757arranged in the thermal coupling plate 751. SNP analyses, for example,can thus be carried out by means of determining melting curves.

Outside the plane of the drawing, the unit formed from the thermalcoupling plate 751, the Peltier element 753 and the cooling unit 755 isconnected to the lower part 719 of the cartridge receptacle. In thiscase, the unit is mounted in resilient fashion, such that it is pressedagainst the cartridge 101 and a good thermal contact between the thermalcoupling plate 751 and the chip module 747 is established.

Moreover, outside the plane of the drawing, sprung contact pins areprovided within the lower part 719 of the cartridge receptacle 103, andtap off electrical signals of the chip module 747 for evaluation.

A practically suitable determination of DNA, proteins and also haptensis now possible with the described system including smart card forsample uptake and evaluation device with control device for sampleprocessing and evaluation when the cartridge has been introduced intothe evaluation device.

Example embodiments being thus described, it will be obvious that thesame may be varied in many ways. Such variations are not to be regardedas a departure from the spirit and scope of the present invention, andall such modifications as would be obvious to one skilled in the art areintended to be included within the scope of the following claims.

The invention claimed is:
 1. Biochip analysis device, comprising: acartridge in the form of a plastic card which contains a system ofmicrofluidic channels that form a reservoir that contains a reactionsubstance, a sample chamber and flow channels, a fluid input covered bya pierceable septum and a cover film overlying the system ofmicrofluidic channels, a control device having a cartridge receptaclefor receiving, locking, unlocking and releasing the cartridge, thecontrol device comprising: a power supply connected to the cartridgereceptacle, a plurality of first sensors adapted for identifying whetheror not a cartridge located in the cartridge receptacle is a correctcartridge and correctly located therein, a means for positioning acartridge inserted into the cartridge receptacle, a plurality of secondsensors which are adapted to emit an externally measurable signalrepresentative of information about an analyte in a cartridge located inthe cartridge receptacle, fill level sensor means for monitoring of theflow of fluid in the cartridge, a microcontroller adapted for controland data acquisition, and having means for transmitting data to anexternal computer, and a pump controlled by the microcontroller andadapted to direct a flow of liquid into and through a cartridge locatedin the cartridge receptacle, wherein the cartridge receptacle iscomprised of upper and lower parts that are movable apart for insertionof a cartridge and together for locking an inserted cartridge in thecartridge receptacle, and wherein a thermostatic regulation device isprovided that has thermal coupling plates at positions adapted fortransferring heat to a cartridge in the cartridge receptacle, a one ofthe coupling plates on a side facing the cover of an inserted cartridgehaving a cutout which enables bulging of the cover film in the event ofexcess pressure within the cartridge.
 2. The biochip analysis device asclaimed in claim 1, wherein interfaces for fluidics and electronics arepresent between the cartridge and the control device.
 3. The biochipanalysis device as claimed in claim 2, wherein the control devicecomprises at least one of at least one serial and one wireless interfacevia which at least one of the signals and at least partly processedsignals are in communication.
 4. The biochip analysis device as claimedin claim 1, further comprising sensors configured to identify a correctorientation of the cartridge in the cartridge receptacle.
 5. The biochipanalysis device as claimed in claim 4, further comprising sensorsconfigured to identify a correct type of the cartridge in the cartridgereceptacle.
 6. The biochip analysis device as claimed in claim 1,wherein a water reservoir configured to dilute the sample, to dissolvedry reagents stored in the cartridge and to carry out flushingoperations in the control device is provided.
 7. The biochip analysisdevice as claimed in claim 6, further comprising a filter to ventilatethe water reservoir when water is drawn.
 8. The biochip analysis deviceas claimed in claim 1, further comprising a hollow needle arranged forpiercing the pierceable septum.
 9. The biochip analysis device asclaimed in claim 1, further comprising capacitive sensors identifyingthe filling of channels on the cartridge.
 10. The biochip analysisdevice as claimed in claim 9, wherein the capacitive sensors includeselectrodes, wherein the electrodes are arranged in such a way that, whenthe cartridge is introduced into the control device, one of theelectrodes is situated above the cartridge and one of the electrodes issituated below the cartridge.
 11. The biochip analysis device as claimedin claim 1, further comprising a closing/opening device configured toclose off and open chambers in the cartridge.
 12. The biochip device asclaimed in claim 11, wherein the closing/opening device configured toclose off and open the chambers are embodied as movable plungers. 13.The biochip analysis device as claimed in claim 1, further comprising amagnetic bead collector configured to capture magnetic beads, whereinthe magnetic bead collector is combined into a unit with thethermostatic regulation device.
 14. The biochip analysis device asclaimed in claim 13, further comprising a contact pressure deviceconfigured to a defined contact pressure between thermostatic regulationmodules and the cartridge.
 15. The biochip analysis device as claimed inclaim 1, further comprising an electrical contact device configured tomake electrical contact with an electrical chip module.
 16. The biochipanalysis device as claimed in claim 15, wherein the electrical chipmodule includes a thermostatic regulation unit.
 17. The biochip analysisdevice as claimed in claim 1, wherein the cartridge is a single-usecartridge.
 18. The biochip analysis device as claimed in claim 1,wherein the cartridge includes a PCR chamber, and a magnetic core islocated directly at a surface of the PCR chamber when the cartridge isinserted in the cartridge receptacle.